JPS6320553B2 - - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION The present invention relates to a device for separating whole blood into its components and automatically collecting one of the components.

Various methods and devices have been proposed to separate whole blood into three types of components within a centrifugal liquid processing device. In these cases, the whole blood is processed by centrifugal force to separate the red blood cells in the outermost radius of the container, the leukocyte buffy coat in the middle, and the platelet-containing plasma in the innermost radius. A rotor assembly having a container for receiving whole blood rotates within the device. The container is provided with outlets at different radial positions, and a tube is connected to the outlet. One radial position and
A pump is provided to draw out each of the blood components that collect in areas adjacent to each outlet. The outlet is connected to the tube either directly or by a liquid seal. When the outlet is connected directly to the tube, the tube is driven by the rotor assembly at twice the speed of the coaxial member carrying the cable retainer through which it reaches the bowl in the rotor assembly. This prevents kinking. A detailed description of a device having such construction and operation can be found in US Pat. No. 3,986,442.

When whole blood is centrifuged, red blood cells are drawn out by one pump, white blood cells are drawn out by another pump, and plasma containing platelets is drawn out by another pump separate from said pump. drawn out. The withdrawal speed of the various pumps depends on the concentration of these components in the blood and on the change in radius at which each component collects during centrifugation. The radius at which these blood components converge changes during centrifugation, so the operator must carefully observe the blood components while they are being withdrawn. For example, when the buffy coat of white blood cells is drawn out,
The operator can see if it is too light, i.e., plasma is not drawn out along with the buffy coat, and if it is too dark, i.e., red blood cells are not pulled out along with the buffy coat. Must check. If the buffy coat is too bright or too dark, the operator will then adjust the speed of the red blood cell pump in one direction and the speed of the plasma pump in the opposite direction. In other words,
One increases the speed and the other decreases the speed so that the desired composition or optical density of the buffy coat is elicited. It requires constant attention from the operator and is somewhat tedious when the operation lasts an hour or more.

As will be described in detail hereinafter, the present invention automatically monitors the composition or optical density of the buffy coat of leukocytes drawn from a centrifuge, and when a change occurs an optical detector detects the desired composition or optical density of the leukocytes drawn. red blood cells, so that optical density is maintained
This need for operator monitoring is overcome by providing a device that operates to adjust the withdrawal rate of platelet-containing plasma.

According to the invention, a device for separating whole blood into its components is provided. The apparatus includes a means for withdrawing whole blood from a donor, a centrifuge, a means for providing the withdrawn whole blood to the centrifuge for centrifuging the whole blood in the centrifuge, and a centrifuge. a first withdrawal means for withdrawing a first blood component enriched in red blood cells from the centrifuge; and a second withdrawal means for withdrawing a second blood component enriched in white blood cells from the centrifuge; third withdrawal means for withdrawing three blood components; means for recombining said first and third blood components and returning said recombined blood components to the donor; means for detecting the composition of a second blood component; and first and third withdrawal means when mixing of the first or third component and the second component is detected by the detection means; and means for collecting the second blood component.

The detection means is an optical pickup having a light source for transmitting light through a light transmitting portion of the tube for extracting the second blood component, and an optical detector for detecting the amount of light transmitted through the light transmitting portion. It includes means.

FIG. 1 is a perspective view of the centrifugal fluid processing device of the present invention.

FIG. 2 is a schematic illustration of the electromechanical control system of the device shown in FIG. 1, including a fluid system and a cross-sectional view of a portion of the device.

FIG. 3 is a schematic circuit diagram of the analog portion of the control circuit shown in FIG. 2.

FIG. 4 is a schematic circuit diagram of the digital portion of the control circuit shown in FIG. 2.

Referring in detail to the drawings, a centrifugal fluid processing apparatus 10 for separating whole blood into its components is generally illustrated in FIG. Apparatus 10 includes a cabinet 12 having a generally cylindrical hole 14 at the top within which a centrifuge is located. Extending from the inner wall of cylindrical bore 14 is a support arm assembly 18 whose outer end is centered over centrifuge 16 . A group of four flexible tubes 20 extend through the outer end of arm assembly 18 for connection to centrifuge 16 .

A preferred embodiment of the invention illustrated in FIG.
It is composed of the following specific measures.

The means for removing whole blood from the donor and supplying it to the centrifuge 16 are the first tube 21 and the peristaltic pump 34.

The centrifuge is centrifuge 16.

The first withdrawal means for withdrawing the first blood component rich in red blood cells from the centrifuge includes a second tube 22 extending from the outlet 52 of the bowl 30 and a first tube 22 driven by a first motor 70. A first motor controller 72 for operating a pump 54 and a first motor 70 is provided.

The second withdrawal means for withdrawing the second leukocyte-rich blood component from the centrifuge comprises a third tube 23 extending from the outlet 58 of the bowl 30 and a second pump 60. The second pump 60 is operated at a constant speed by a second motor and a second motor controller (not shown).

A third withdrawal means for withdrawing a third plasma-enriched blood component from the centrifuge includes a fourth tube 24 extending from the outlet 64 of the bowl 30 and a third tube 24 driven by a third motor 80. pump 6
6 and a third motor controller 82 for operating a third motor 80.

The means for recombining the first and third blood components, red blood cells and plasma and returning the recombined blood components to the donor, includes a Y-shaped fitting 56 where tubes 22 and 24 meet; A tube 68 is provided for connection to a blood donor.

The means for detecting the composition of the extracted blood components includes a light source 90 for transmitting light through the transparent portion of the tube 23, a light pipe 92, and an optical pickup device 100.

When the mixing of the second blood component and another blood component is detected by the detection means, the means for adjusting the withdrawal speed of the first and third withdrawal means is configured to adjust the withdrawal speed of the first and third withdrawal means. Motor control tool 7
2 and 82 is provided.

The means for collecting the second blood component, white blood cells, is a bag 62 connected to one end of tube 23 downstream of pump 60.

The configuration and operation of the above specific means will now be explained in more detail.

As best shown in FIG. 2, the tube group 20 includes four tubes extending from the arm assembly 18 through a tubular sleeve 26 attached to the side of the vessel holder 28 of the centrifuge 16. Consists of 21, 22, 23 and 24. Mounted within the centrifuge 16 is a closed bowl 30 having a hollow inner chamber 32 within which whole blood is centrifuged, as will be described in detail below.

Referring to FIG. 2, the first tube 21 is
It passes through and forms part of a peristaltic pump 34 which is connected to the donor 33 in a conventional manner and is operative to draw whole blood from the donor 33. Although not shown, generally reference numeral 35 of device 10
It is understood that appropriate low and high pressure detectors are provided within the tube to detect high and low pressure conditions signifying a leak in the fluid system or occlusion of the donor's veins as represented by Will. When such a condition is detected, the low pressure and/or high pressure detectors are activated to stop operation of the device 10.

After leaving the peristaltic pump 34, the tube 21 is guided into the device 10 and onto the arm assembly 18 below the latch member 36. The latch member 36 is part of the arm assembly 18 and holds the arm assembly in place while simultaneously locking the tube 2.
1 to 24 are held on the arm assembly 18. From there, the tube 21 passes over a tube guide member 38 mounted on the arm assembly 18 and then extends through a hole in a tube holder 40 located at the outer end of the arm assembly 18. The tube 21 then connects to the tube-like sleeve 2
6 and enters a passageway 42 formed in a rotor drive shaft 44 for centrifuge 16 .

As shown, the passageway 42 is L-shaped and extends radially inward from the side of the drive shaft 44;
The drive shaft 44 then points axially upwardly and then engages a hole 46 in the container holder 28 and through the engaging hole 48 to the bottom of the bowl 30 where an inlet 50 to the hollow interior 32 of the bowl 30 is opened. connected to.

Within the bowl 30, the blood from the donor is collected such that the red blood cells collect at the outer radial position, the buffy coat of the white blood cells collect at the middle radial position, and the plasma containing platelets collect at the inner radial position within the hollow portion 32 of the bowl 30. Whole blood is centrifuged by rotation of bowl 30. An outlet 52 is provided on the upper edge of bowl 30 at the outer radius and adjacent the area where red blood cells collect. A second tube 22 is connected to this outlet 52 and from there passes through passages 48 and 42, sleeve 26, perforated holder 40, guide member 38.
above, below the latch member 36 and passing through and becoming part of the peristaltic pump 54 and extending therefrom to the Y-connection 56 .

In a similar manner, the third tube 23 is
0 and is connected to an outlet 58 located at an intermediate radius on the upper edge of the bowl 30 and adjacent to the area where the leukocyte buffy coat collects in the hollow interior of the bowl 30. Tube 23 then passes through passages 48 and 42, sleeve 26, perforated holder 40, over guide member 38, latch member 36.
and passes through and becomes part of a peristaltic pump 60 and reaches a white blood cell collection bag or container 62.

Again in a similar manner, the fourth tube 24 is connected to an outlet 64 located at the upper edge of the bowl 30 at the inner radius where the plasma collects. tube 24
from the passageways 48 and 42, the sleeve 26,
A perforated holder 40, the upper side of the guide member 38,
The tube 24 passes under the latch member 36 and then passes through and forms part of a peristaltic pump 66 from which the tube 24 is recombined with plasma and red blood cells and returned to the donor 33 via tube 68. extending to the figure-shaped fitting 56 .

As shown, the peristaltic pump 54 is connected to the motor 7
0 and the speed of the motor is controlled by motor controller 72. The control tool 72
is actuated by a first rotary control rod 74 having a knob 76 at its outer end for manual control thereof. Typically, the motor controller 72 is an adjustable potentiometer having a rotating sweep arm rotatably attached to a rod 74 such that rotation of the knob 76 adjusts the potentiometer, thereby controlling the motor controller 72.
motor 70 to change the speed of pump 54
includes an adjustable potentiometer adapted to vary the speed of the

Similarly, peristaltic pump 66 is driven by a motor 80 whose speed is controlled by a motor controller 82 having a second rotary control rod 84 extending therefrom. The rod 84 also has a tab 86 at its outer end. In a manner similar to motor controller 72, motor controller 82 causes motor controller 82 to vary the speed of motor 80, thereby increasing the speed of pump 66.
The potentiometer has a rotating sweep arm rotatably connected to the rod 84 so as to adjust the potentiometer setting by rotation of a knob 86 to change the speed of the potentiometer.

In accordance with the teachings of the present invention, a light source 90 and a light pipe (optical fiber) 92 transmit light from the light source 90 to a passageway 94 within the latch member 36. The passageway 94 opens into a groove 96 in the latch member 36 that is aligned with a projection 98 attached to the arm assembly 18. The protrusion 98 holds the light transmitting portion of the tube 23 within the groove 96;
Therefore, light entering passageway 94 passes through the light-transmissive portion of tube 23 and passes to optical pickup 100 within alignment passageway 94 provided in latch member 36. Therefore, the optical density of the white blood cells drawn through the tube 23 is
Detected and monitored by 0. Optical pickup 100 can be a fiber optic pipe or a detector with electrical leads. In either case, FIG. 2 shows an extension of the device 100, ie, a line 102 from the optical pickup device 100, which may be a fiber optic pipe or an electrical conductor, and is connected to a control circuit 104. As will be described in detail below, the control circuit 104 is connected to the second gear 10.
The gear drive motor 106 connected to the gear drive motor 106 is operated to drive a gear drive motor 106 connected to Gear 108 is adapted to mesh with a third gear 110 on second control rod 84 as shown in FIG. 2, which in turn is adapted to mesh with first gear 112 on first control rod 74. are doing.

The control circuit 104 controls the optical pickup device 100.
It is determined whether the light (optical density) received by the optical density is within a predetermined range and whether the optical density is increasing or decreasing. Then depending on the detected optical density and whether it is increasing or decreasing,
The control circuit 104 includes a motor 106 and a gear 1
08 to cause various rotations, thereby causing gear 110 to rotate clockwise or counterclockwise, and gear 112 to rotate counterclockwise or clockwise. Such rotation of gears 110 and 112 will adjust the potentiometers of motor control circuits 82 and 72, producing a change in the speed of motors 80 and 70, but in opposite directions. Therefore, when the speed of motor 80 increases or decreases, the speed of motor 70 decreases or increases. Briefly summarizing the operation of the electromechanical system of device 10, when the density of leukocyte buffy coat being drawn darkens beyond a predetermined range that defines the desired composition of the buffy coat, the control circuit 104 increases the speed of motor 70 and decreases the speed of motor 80, thereby drawing more red blood cells and less plasma from bowl 30. This method maintains a buffy coated area of leukocytes having the desired composition at the radial location of outlet 58.

In a similar manner, control circuit 104 causes motor controller 82 to control motor controller 82 when the sensed buffy coat optical density falls below a predetermined range, indicating that there is more than the desired amount of plasma in the buffy coat. causing motor 106 to rotate gear 108 to increase the speed of motor 80 and cause motor controller 72 to decrease the speed of motor 70, thereby withdrawing more plasma and less red blood cells and less white blood cells. An area of buffy coat having the desired composition is maintained at the radial location of outlet 58.

To provide greater flexibility to device 10, rod 84 can be moved axially between three positions. The first position is where gear 110 meshes with gear 108 and gear 112, as shown by the solid line in FIG. In the second position, the rod 8
4, the gear 110 shown in phantom has been moved inward toward the motor controller 82 to a position where it does not mesh with the gear 108 but only with the gear 112. In this position, pumps 54 and 66
only manual adjustment of the speed of the knob 86 can be made, and in this position the adjustment of the knob 86 is similar to that of the other knob 7.
6 is also adjusted at the same time, but in the opposite direction.

In the third position, gear 110, again shown in phantom, does not engage either gear 108 or gear 112. In this position, pump 5
4 and 66, and the respective withdrawal rates of fluid through tubes 22 and 24, are independently controlled by knobs 86 and 76, respectively.

Referring now to FIG. 3, analog circuitry 118 of control circuit 104 is illustrated. Analog circuit 118 may include a phototransistor 120 that receives light from optical pickup device 100;
Alternatively, the phototransistor 120 may be built into the optical pickup device 100. Phototransistor 1
The signal generated by 20 is amplified by an amplifier circuit 124 and passed through conductors 125 and 126 to a first comparison means for comparing the amplified signal with a first reference voltage established by a voltage divider 130. It is applied to a certain first comparison circuit 128 . This is a high level voltage to determine the upper limit of a predetermined range of optical density. The amplified signal is also applied to a second comparator circuit 132, which is a second comparison means that compares the output signal to a low level voltage established by a potentiometer 134.

The amplified signal at the output of amplifier circuit 124 is also applied to differentiator circuit 136 . Differential circuit 1
The output from 36 is then applied via conductor 138 to a third comparison circuit 140 that compares the differentiated output signal to a high reference voltage established by voltage divider 142. . The differentiation circuit 1
The same output signal from 36 divides said signal into voltage divider 1
It is also applied to a fourth comparator circuit 144, which is a fourth comparator means for comparison with a low reference voltage established by 46.

Differentiator circuit 136 includes a first sample and hold circuit 148, a second sample and hold circuit 150, and a comparator circuit 152. Sample and hold circuits 148 and 150
The output of the fifth comparison means is applied to a comparator circuit 152.

There is a first gate 154 connected to the input to the first sample and hold circuit 148 and a second gate 156 connected to the input to the second sample and hold circuit 150. Furthermore, gates 161, 162,
163 and 164 are connected.

The analog circuit 118 also includes a clock 168 having a first output 1, a second output 2 and a third output 3 as gate signal generating means.
the first output 1 is connected to the first gate 154;
the second output 2 is connected to the second gate 156;
And the third output 3 is the comparator circuit 128, 13
2, 140 and 144 to gates 161-164, which are connected to the outputs of signals 2, 140 and 144, leading to signal output conductors 171-174.

In operation of the analog circuit shown in FIG. is closed by a short pulse from output 1 of . At a second point in time, about one minute later, another short pulse is applied to gate 156 for a short period of time to position a second sampling of the amplified signal that will appear at a later point into second sample and hold circuit 150. Appears on output 2 of the clock to close the clock. Comparator circuit 152 then compares the outputs of sample and hold circuits 148 and 150 and determines whether the amplified signal is increasing or decreasing. If the comparator circuit 152 is increasing, the comparator circuit 152
3 will generate a high level signal which will be sensed by the third comparator circuit 140 to generate a high logic output signal to be provided to the third comparator circuit 140. If the amplified signal is decreasing, the comparator circuit 152 decreases the low voltage that would be sensed by the fourth comparator circuit 144 to generate a high logic output signal to be provided on conductor 174. will generate an output signal.

Immediately after the second gate 156 closes, the gate pulse from output 3 is applied to the gates 161, 162, 163.
and 164, so that all signal levels are now applied by control circuit 104 to the digital circuitry of FIG. 4, generally identified by reference numeral 175.

Turning now to FIG. 4, the digital circuit 17
5 is the output conductor 171, 172, 17 from the four comparison means 128, 132, 140 and 144.
The four inverter circuits 181 to 184 are connected to each other, one each of 3 and 174. Digital circuit 175 also includes six ANDs.
Also includes circuits 191-196. As shown, comparator circuits 128, 132, 140 and 14
4 and inverters 181 to 184
The output thereof is connected to each AND circuit 191 to 196. Each output from AND circuits 191 to 196 is connected to six univibrator circuits 2
01 to 206. First three univibrator circuits 201
The outputs of 203 to 203 are sent to three inverters 21
1, 212 and 213, respectively.
Similarly, univibrator circuits 204, 2
The outputs of 05 and 206 are supplied to three inverter circuits 214, 215 and 216, respectively. As shown, the outputs from the inverters 211-213 are connected to the first electronic device, the so-called "light", connected to the gear drive motor 106.
It is supplied to an OR circuit 218 which feeds into a control circuit 220. Phototransistor 120 (FIG. 3) provides a high level signal on conductor 171 when the optical density of the buffy coat of white blood cells is low, which is an indication of plasma mixing in the buffy coat, and such signal is When sent by the first OR circuit 218 to the control circuit 220, the "bright" control circuit 220
operates the gear drive motor 106 to decrease the speed of the motor 70 that controls the pumping of red blood cells and simultaneously increase the speed of the motor 80 that controls the pumping of plasma, thereby increasing the optical density of the buffy coat. Since the control circuit 22
0 is called a "bright" control circuit.

Similarly, inverter circuits 214 to 21
The output of 6 is fed to an OR circuit 222, the output of which is fed to a second electronic device, the so-called "dark" circuit.
Connected to control circuit 224. This "dark" control circuit 224 is configured such that a "low" signal indicating high optical density passes through an OR circuit 222 to the "dark" control circuit 224.
Activates when sent to 4. This signal activates control circuit 224 to increase the speed of motor 70 for pump 54 for pumping red blood cells and to decrease the speed of motor 80 controlling pump 66 for pumping plasma. reduces the density of the buffy coat that is aspirated from the bowl 30 under detection.

Univibrators 201-203 and univibrators 204-206 have different output pulse widths. To this end, univibrator 201 generates a maximum width output pulse to produce maximum rotation in motor 106 to reduce the speed of pump 54 pumping the red blood cells. Univibrator 202
generates a medium width pulse to impart a medium rotation to motor 106 resulting in a medium reduction in the speed of pump 54, and univibrator 203 causes a small reduction in the speed of pump 54. The motor 106 generates a minimum width pulse to produce a small rotation.

Similarly, univibrator 204 generates large width pulses, univibrator 205 generates medium width pulses, and univibrator 206 generates small width pulses, each of which provides a large width pulse to motor 106. ,During,
Large, medium,
causes a small increase.

Decreasing or increasing the speed of the pump 54 for pumping red blood cells by degrees is controlled by the gear 1
It will be appreciated that there is a corresponding decrease or increase in the speed of the pump 66 that draws plasma-laden platelets from the bowl 30 at the same time as the interlocking engagements of 08, 110 and 112.

A review of the circuit connections in the digital circuit 175 of FIG. 4 reveals that the digital circuit 175 operates in the manner described below to adjust the withdrawal rate of red blood cells and plasma in response to different sensing. .

A When the detected optical density is above a predetermined range and increasing, a large reduction in the withdrawal rate of red blood cells is carried out, and at the same time a corresponding increase in the withdrawal rate of plasma.

B A moderate reduction in the withdrawal rate of red blood cells is carried out when the optical density is within a predetermined range, but increasing, and at the same time a corresponding increase in the withdrawal rate of plasma.

C. When the optical density is not increasing but exceeds a predetermined range,
A minimal reduction in the withdrawal rate of red blood cells is carried out, with a corresponding increase in the withdrawal rate of plasma at the same time.

D When the optical density is below a predetermined range and decreasing, a large increase in the withdrawal rate of red blood cells is carried out, and at the same time a corresponding decrease in the withdrawal rate of plasma.

E When the optical density is within a predetermined range, but decreasing, a moderate increase in the withdrawal rate of red blood cells is carried out, and at the same time a corresponding decrease in the withdrawal rate of plasma.

When the F optical density falls below a predetermined range and remains unchanged, a minimal increase in the withdrawal rate of red blood cells is carried out, and at the same time a corresponding decrease in the withdrawal rate of plasma.

It will be clear from the above description that the device of the present invention provides automatic and effective collection of white blood cells. It will also be apparent to those skilled in the art that obvious modifications and changes may be made to the apparatus of the present invention without departing from the teachings of the invention. Accordingly, the scope of the invention is limited only by the claims.

[Brief explanation of the drawing]

FIG. 1 is a perspective view of a centrifugal fluid processing device of the present invention;
2 is a schematic diagram of the electromechanical control system of the device shown in FIG. 1, FIG. 3 is a circuit diagram of the analog part of the control circuit of FIG. 2, and FIG. 4 is a circuit diagram of the digital part of the control circuit. be. 10 is a centrifugal fluid processing device, 16 is a centrifuge, 18
is an arm assembly, 20 is a tube group, 30 is a bowl, 34, 54, 66 are peristaltic pumps, 72,
82 is a motor controller, 90 is a light source, 100 is an optical pickup device, 104 is a control circuit, 118 is an analog circuit, and 175 is a digital circuit.

Claims (1)

[Scope of Claims] 1. A device for separating whole blood into its constituent components, comprising: a centrifuge 16 for separating whole blood into its constituent components having different densities and collecting them in areas having different radial distances from the axis of rotation; and means 21, 34 for removing whole blood from a donor and supplying the removed whole blood to said centrifuge 16 for separation of the whole blood in said centrifuge 16, and said centrifuge 16 enriched with red blood cells. First withdrawal means 22, 54 for withdrawing a first blood component
and second withdrawal means 23, 60 for withdrawing a second blood component rich in white blood cells from the centrifuge 16.
and third withdrawal means 24, 66 for withdrawing a third plasma-enriched blood component from said centrifuge 16.
and means 56, 68 for recombining said first and third blood components and returning the recombined blood components to the donor; and means for detecting the composition of the withdrawn second blood component. A light source 90 for transmitting light through a light transmitting portion of the tube 23 for extracting a second blood component, and an optical detector for detecting the amount of light transmitted through the light transmitting portion. a pickup means 100; and when the detection means detects a mixture of the second blood component and another blood component, the first and third withdrawal means are pulled out. means 72, 82, 104 for adjusting the speed; and means 62 for collecting a second blood component, each of said first blood component, second blood component and third blood component; Withdrawal means 22, 54: 2
3,60: 24,66 are connected in parallel to each other to the centrifuge 16 and means 21,3 for supplying whole blood taken from said donor to the centrifuge;
Apparatus for separating whole blood into its constituent components, characterized in that it is connected in series via a centrifuge 16 to a centrifuge 16. 2 The first pulling means is a first motor 7
0 and a first motor control means 72 for operating said first motor 70, said second withdrawal means being controlled by said second control means. comprising a second motor-driven pump 60 operating at a constant speed, said collection means comprising a container 62 connected to the output of said second pump 60, and said third withdrawal means comprising a third pump 66; , a third motor 80 for driving said third pump 66, and third motor control means 82 for operating said third motor, and said means for adjusting said withdrawal speed First and third motor control means 72, 82
including control circuit means 104 connected to said sensing means 90, 100 for regulating first and third motor control means 72, 82 to regulate the speed of said first and third pumps 54, 66; The control circuit means 104 operates in response to the amount of light detected by the detection means 90, 100.
2. The apparatus of claim 1, wherein the apparatus is connected to a . 3. The first motor control means includes an electrical speed control circuit 72 having a rotatable mechanical control 76 for adjusting the speed of the first motor 70, and an electrical speed control circuit 72 extending from the mechanical control. a first rotatable control rod 74 having a first gear 112 attached to it and a second gear 10 on its output shaft;
a gear drive motor 106 having a gear drive motor 8;
06, said third motor control means includes an electrical speed control circuit 82 having a rotatable mechanical control 86 for adjusting the speed of said third motor 80; a second rotatable control rod 84 extending from tool 86; and a third rotatable control rod 84 attached to said second control rod 84 and adapted to engage said first and second gears 112, 108. a gear 110, and the control circuit means 104 causes the gear drive motor 106 to move the second gear 108 by a predetermined arcuate distance in response to the amount of light detected by the detection means 90, 100. The third gear 110 is rotated in one direction, and the meshing engagement between the third gear 110 and the first gear 112 is activated. Said first motor control means 72 such that the first gear 112 also rotates at the same time, but in the opposite direction, thereby causing the first motor 70 to increase or decrease the speed of the first pump 54.
while simultaneously adjusting the speed of said third pump 6
6 and the desired composition of the second blood component, i.e. buffy coat, is increased or decreased in the second pump 60.
3. Apparatus according to claim 2, adapted to adjust the speed of said third motor 80 so as to be drawn by said third motor 80. 4. The first control rod 74 has a first knob 76 at its outer end for manually operating the first motor control means 72, and the second control rod 84 has a first knob 76 for manually operating the first motor control means 72. 82 has a second knob 86 at its outer end for manual operation of the control rod 82, said second control rod 84 being capable of axial movement in three positions; gear 1
10 is a position where the third gear 110 engages with both the first gear 112 and the second gear 108, and the second position is where the third gear 110 engages with the first gear 11.
2, and a third position where the third gear 110 engages only with the first gear 112.
Alternatively, it is a position in which the second gear 108 is not engaged, and therefore, in the first position, the speeds of the first and third pumps 54, 66 are automatically controlled by the detection means 90, 100. and in the second position control of the speed of the first and third pumps 54, 66 results in an adjustment of one of said knobs 76, 86 causing an opposite adjustment of the other knob. Accordingly, it is achieved by manual operation, and in the third position said first motor control means 72 as well as said third motor control means 82 are independently controlled by said knobs 76, 86. Apparatus according to paragraph 3. 5 said means for supplying whole blood to said centrifuge 16 comprises a first tube 21 connected to the donor and extending into said centrifuge for delivering whole blood to said centrifuge 16;
said first withdrawal means comprises a second tube 22 connected to an outlet 52 of said centrifuge located adjacent to an area where red blood cells collect in said centrifuge.
said second tube 22 extends outwardly from said centrifuge for returning red blood cells to a donor, and said second withdrawal means is located adjacent an area within said centrifuge where leukocyte buffy coats collect. a third tube 23 connected to the outlet 58 of the centrifuge, the third tube 23 extending outwardly from the centrifuge and connected to the collection means 62, and connected to the third drawer 62; The means includes a fourth tube 24 connected to an outlet 64 of the centrifuge adjacent to the area where plasma and platelets collect in the centrifuge, the fourth tube extending outwardly from the centrifuge to collect blood. 5. A device according to any one of claims 1 to 4, connected to said second tube (22) for recombining red blood cells, platelets and plasma for return to a person. 6. A support arm 18, wherein the four flexible tubes 21, 22, 23, 24 are fixedly supported on the support arm and extend from there into the centrifuge 16. equipment. 7 a light source 90 and the support arm 1 adjacent to the light transmitting portion of the third tube 23 from the light source;
means 92 for directing light to a position 8; and a light pick-up provided on the support arm 18 on the other side of the light-transmissive portion of the third tube 23 and in line with the light directing means. 7. Apparatus according to claim 6, comprising means (100), said pick-up means including said sensing means operative to generate an electrical signal supplied to said withdrawal speed regulating means (104). 8. said sensing means 90, 100 is operative to generate an electrical signal, and said control circuit means includes an amplifying means 124 for amplifying said electrical signal, and amplifying means 124 for amplifying said electrical signal; a first comparing means 128 operable to compare said amplified signal to a reference voltage and generate a logic output signal when said amplified signal exceeds said first reference voltage; a second comparison means 132 for comparing the amplified signal with a reference voltage of the second reference voltage and generating a theoretical output signal when the amplified signal is less than or equal to the second reference voltage; differentiating the amplified signal to determine whether it is increasing or decreasing, and generating a low logic signal when the amplified signal is decreasing over a predetermined period of time; differentiating means 136 for generating a high logic signal when increasing over a predetermined period of time; and comparing said differentiated output signal with a third reference voltage and determining that said amplified signal is increasing. a third comparison means 140 for generating a logic output signal indicative of , and comparing said differential output signal with a fourth reference voltage and generating a logic output signal when said amplified signal is decreasing; and digital circuit means 175 connected to the outputs of said four comparison means 128, 132, 140, 144 for generating a plurality of output signals, said digital circuit means A first electronic device 220 having two outputs, one output for causing the gear drive motor 106 to rotate in one direction.
and the other output is connected to a second electronic device 224 for causing the gear drive motor 106 to rotate in the opposite direction, and the digital circuit means 175 is connected to the four comparison means 128. , 132, 140, 144 to generate six control signals, three of which are applied to the first output and which are applied to the second gear 108. The speed of the first pump 54 is reduced as desired by producing three different amounts of rotation in one direction, for example large rotation, medium rotation or small rotation, and the speed of the third pump 66 is correspondingly reduced. the remaining three signals cause the second gear 108 to rotate in three different amounts in opposite directions, e.g., large rotation, medium rotation, or small rotation, thereby increasing the speed of the first pump 54. The particular control signal generated is determined by the first 128 or the second comparison means 132. determined by whether a high signal or a low signal is detected, and whether an increasing amplified signal is detected by said third 140 and fourth comparison means 144; 4. The apparatus of claim 3, wherein the determination is determined by whether a decreasing amplification signal is detected. 9. The differentiating means 136 includes a first sample and hold circuit 148 for sampling the amplified signal at one point in time and a second sample and hold circuit 148 for sampling the amplified signal at a second point in time. a sample and hold circuit 150, the outputs of both sample and hold circuits producing a logic high signal when the amplified signal is increasing and a logic low signal when the amplified signal is decreasing. fifth comparison means 15 for generating a signal and operative to generate a zero value signal when there is no change in the amplified signal;
2. The device according to claim 5, which is connected to 2. 10 Said first sample and hold circuit 1
a first gate 154 at the input to said second sample and hold circuit 150 and said first, second, third and fourth comparison means 128; ,130,
gating means 161, 162, 163, 164 provided at the respective outputs of 140, 144 and a first gate supplied to said first gate for opening said first gate 154 at a first time; a second gate signal applied to the second gate to open the second gate 156 at a second time; and a second gate signal applied to the second gate 156 at a third time; Four comparison means 128, 130, 14
Said gate means 1 provided at the output of 0,144
7. The apparatus of claim 6, further comprising gate signal generating means (168) operative to periodically generate a third gate signal to be supplied to the gates (61, 162, 163, 164). 11. The digital circuit means includes inverter circuits 181, 182, 18 connected to the outputs of the four comparison means 128, 130, 140, 144.
3,184 and AND circuit means 191 to 19 connected to the inverter circuit and the comparison means.
6, and the AND circuit means includes six AND circuits each connected to a univibrator circuit 201-203, the first, second and third univibrator circuits 201-20
3 is a first pump 54 that pumps red blood cells;
gear drive motor 106 in the direction of decreasing the speed of
is connected to a first OR circuit 218 which is connected to a "light" control circuit 220 to rotate
The first univibrator circuit 201 generates pulses that cause the gear drive motor 106 to rotate in large rotations so as to cause a significant reduction in the speed of the first pump 54, and the second univibrator circuit 202 , the first pump 54
, and the third univibrator circuit 203 generates a pulse that causes a moderate rotation in the gear drive motor 106 to produce a moderate reduction in the speed of the first pump 54 . The fourth, fifth and sixth univibrator circuits 204-206 generate pulses that cause a small decrease in the rotation of the gear drive motor 106 to reduce the speed of the first pump 54. , said fourth univibrator circuit 204 is connected to a "dark" control circuit 224 for increasing said first pump 5
The fifth univibrator circuit 205 generates a pulse that causes a large rotation in the gear drive motor 106 to cause a large increase in the rotational speed of the first pump 54 . The gear drive motor 1 to bring about
06, and generates a pulse causing a moderate rotation in the sixth univibrator circuit 2.
06 generates a pulse that causes a small increase in the speed of the first pump 54, and the third pump 66 generates a pulse that causes a small increase in the speed of the first pump 54, respectively changing the speed of the first pump 54 as described above. , the meshing engagement of the second and third gears 108, 110, 112 to cause equal but opposite rotation.